Method and device for the intermittent occlusion of the coronary sinus

ABSTRACT

In a method for intermittently occluding the coronary sinus, in which in an alternating manner the coronary sinus is occluded by an occlusion device and the occlusion is released, the curve of the fluid pressure occurring in the coronary sinus after the release of the occlusion is estimated by calculation and the time of the beginning of the next occlusion is determined as a function of the estimated pressure curve.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of and claims priority to U.S. application Ser. No. 13/488,630, filed on Jun. 5, 2012, which is a continuation of and claims priority to U.S. application Ser. No. 13/404,810, filed on Feb. 24, 2012, which is a divisional application of and claims priority to U.S. application Ser. No. 11/629,401, filed on Aug. 16, 2007, which is the U.S. national phase of International Application PCT/AT2005/000203, filed on Jun. 7, 2005, which designated the U.S. and claims benefit of AT A 1012/2004, filed Jun. 14, 2004, the entire contents of which are hereby incorporated by reference.

TECHNICAL FIELD

The invention relates to a method for intermittently occluding the coronary sinus, in which in an alternating manner the coronary sinus is occluded by an occlusion device and the occlusion is released, as well as a device for the intermittent occlusion of the coronary sinus.

BACKGROUND

Arterial blood, which supplies the heart muscle, is able to pass through healthy heart tissue while nourishing the same, yet has difficulty reaching ischemic tissue. As a result, the supply of ischemic tissue with nutrients and the discharge of metabolic catabolites from such ischemic tissue will be impaired.

In this context, it has already been proposed to supply ischemic tissue with blood through retrograde perfusion. This means that blood is tried to be allowed to flow back from the coronary sinus through the coronary venous system in counterflow by feeding blood from a different source into the coronary sinus, either by permanently connecting an artery with the coronary sinus or by temporarily inserting a catheter into the sinus, which catheter is supplied with blood taken from a remote artery and transported by the aid of a blood pump located outside the patient's body.

Another technique proposed for retroperfusion uses an inflatable balloon which is fixed to the end of a catheter to intermittently occlude the coronary sinus. The blood pressure in the coronary sinus rises during the occlusion at every heart beat so as to cause blood reaching the coronary sinus through the healthy tissue of the heart muscle to be flushed back into the ischemic tissue. For such an intermittent coronary sinus occlusion, the balloon end of the catheter is inserted either percutaneously or surgically. The other end of the catheter is supplied with a gas or fluid by a pump which causes the cyclic inflation and deflation of the balloon.

A typical application of blood retroinfusion in coronary veins through intermittent coronary sinus occlusion applies to myocardial protection during a short-term coronary arterial occlusion in the context of a cardiologic intervention. A typical such intervention comprises, for instance, the balloon dilatation of an arteriosclerotically constricted coronary artery. That method, which is also known as percutaneous transluminal coronary angioplasty (PTCA), comprises the conduction of a balloon catheter into the region of the coronary artery stenosis under X-ray control and the compression of the osclerotic plaque by the inflation of the balloon, which is located on the end of the catheter. During the dilatation of the balloon, no supply of the tissue with oxygen-containing blood takes place downstream in the artery with functional changes in the ischemic area of the myocard being detectable already at dilatations lasting longer than 30 seconds. Consequent″ial problems of the ischemic protection of the myocard will also be faced with at other interventions aimed at coronary vascularization such as, e.g., atherectomy, coronary endoprostheses, laser applications and percutaneous valvular surgeries.

A device for the retroinfusion of coronary veins is, for instance, known from EP 230 996 A2, by which a pressure-controlled, intermittent coronary sinus occlusion can be performed. The device comprises a means for occluding the sinus such as, e.g., an inflatable balloon catheter, a pressure measuring unit for measuring the fluid pressure within the coronary sinus and a control unit which generates triggering signals for the occlusion device to trigger or release an occlusion. The control unit is devised in a manner that the pressure maximum in the coronary sinus is measured during every heart beat, a plateau value of the pressure maxima of consecutive heart beats is estimated by calculation and the occlusion of the coronary sinus is released on the basis of the plateau value of the pressure maxima.

The occlusion of the coronary sinus causes a pressure increase and, as a result, a retroperfusion of blood via the respective vein into the nutritive capillaries of the ischemic area so as to enable the supply of nutrients to that area. At a release of the occlusion, the retroperfused blood is flushed out with the metabolic waste products being carried off at the same time. In the method according to EP 230 996 A2, a systolic pressure curve is, thus, estimated based on the measurement of the pressure maximum in the coronary sinus during every heart beat, whereby the occlusion of the coronary sinus is released as a function of the plateau value of the systolic pressure curve.

In order to determine the time at which the occlusion is to be triggered again, an empirically acquired formula is proposed according to the method of EP 230 996 A2, which allows for an estimation of the interval between the end of the occlusion and the peak value of the reactive hyperemia. This empirically acquired formula is based on parameters of the systolic and diastolic pressure curves determined for the occluded coronary sinus, with a linear regression being performed subsequently. By the method according to EP 230 996 A2 it has become possible to retrigger the occlusion only after the occurrence of the peak value of the reactive hyperemia, i.e. after the impounded blood has streamed out of the coronary sinus. Yet, due to the inaccuracy of the empirically determined formula, the time until the next occlusion of the coronary sinus will occasionally be chosen too long for safety reasons, which means that it will be waited too long “before triggering the next occlusion. That method has, thus, become inefficient, apart from the fact that the calculational implementation of the method has turned out to be cumbersome and not accomplishable at an adequate speed.

SUMMARY

The present invention aims to propose a method and device for the intermittent occlusion of the coronary sinus, which provide an increased accuracy in the determination of the optimal time for the triggering of the next occlusion, while directly taking into account the pressure conditions prevailing in the non-occluded coronary sinus.

To solve this object, the method according to the invention essentially consists in that the curve of the fluid pressure occurring in the coronary sinus after the release of the occlusion is estimated by calculation and the time of the beginning of the next occlusion is determined as a function of the estimated pressure curve. The respective device according to the invention includes an occlusion device for the alternate occlusion of the coronary sinus and release of the occlusion as well as a control device for delivering control signals to the occlusion device to control the time of the beginning and release of the occlusion and is characterized in that the control device is connected with an arithmetic unit configured to calculationally estimate the curve of the fluid pressure occurring in the coronary sinus after the release of the occlusion, wherein the time of the beginning of the next occlusion is determined as a function of the estimated pressure curve. In accordance with the invention, the pressure conditions in the coronary sinus during the non-occluded phase (release phase) are, thus, immediately estimated to determine the time of the beginning of the next occlusion, and it is, therefore, no longer necessary to resort to empirically acquired formulae such that the accuracy of the method will be enhanced. The knowledge or prediction of the curve of the pressure prevailing in the coronary sinus during the release phase allows for direct conclusions as to various other parameters that are decisive for the method, such as, for instance, the flow volume and the peak value of the reactive hyperemia, and permits the precise control of the occlusion device.

A further refinement of the method according to a preferred embodiment is provided in that the pressure maxima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion are estimated by calculation and the time of the beginning of the next occlusion is determined as a function of the estimated pressure maxima—It is feasible to proceed in a similar manner by replacing the pressure maxima with the pressure minima. For the realization of this preferred method, the configuration is further developed such that the arithmetic unit is configured to estimate the pressure maxima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the time of the beginning of the next occlusion is determined as a function of the estimated pressure maxima.

After the release of the occlusion, a relaxation process takes place in the coronary sinus, whereby the pressure curve can be approximated by an exponential function. According to a preferred mode of procedure, it is therefore contemplated that the pressure maxima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion are approximated by an exponential function and the time of the beginning of the next occlusion is determined as a function of the plateau value of said exponential function. The respective device is further developed in a manner that the arithmetic unit is configured to approximate by an exponential function the pressure maxima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the time of the beginning of the next occlusion is determined as a function of the plateau value of said exponential function. In doing so, it may again be proceeded in an analogous manner for the approximation of the pressure minima. The exponential function connecting the pressure maxima or pressure minima and, hence, reflecting the systolic or diastolic pressure curve, respectively, asymptotically approaches a plateau value corresponding to the lowest pressure in the coronary sinus after the release of the occlusion or the starting pressure in the coronary sinus prior to the: initiation of the intermittent occlusion, respectively. This plateau value is, therefore, particularly suitable for the determination of the occlusion intervals. According to a further preferred embodiment, it may, for instance, be proceeded in a manner that the occlusion of the coronary sinus is released as the exponential function reaches a defined multiple of the forecast plateau value. In this case, the release phase is terminated as the pressure in the coronary sinus, according to the forecast exponential curve, exceeds the plateau value by a certain percentage. The respective exponential function in a particularly preferred manner will be defined by:

p(t)=a+b·e ^(−t/c),

-   -   a being the systolic or diastolic pressure in the coronary sinus         prior to the intermittent occlusion,     -   b being the difference between the systolic or diastolic         pressure at the end of the occlusion and the pressure a,     -   c being a time constant.

To this end, only the three parameters a, b and c need be determined, wherein two of the three parameters, namely the parameters a and b, are measurable quantities detectable during an intervention. And c represents a time constant corresponding to the time in which the coronary sinus pressure drops to i/e=36.8% of its maximum value. Due to the fact that two of these three parameters constitute measurable quantities to be ‘determined individually for each patient, the above-mentioned exponential function provides a particularly stable method which yields reproducible values for the occlusion intervals. With a view to providing as precise an approximation as possible, of the exponential function to the actually occurring pressure maxima, the time constant c in this case can be determined using an approximation algorithm.

BRIEF DESCRIPTION OF DRAWINGS

In the following, the invention will be explained in more detail by way of an exemplary embodiment illustrated in the drawing. Therein:

FIG. 1 is a diagrammatic view of a heart including a device for the intermittent occlusion of the coronary sinus;

FIG. 2 is a graphical representation of the coronary sinus pressure curve; and

FIG. 3 depicts the upper envelope of the pressure curve.

DETAILED DESCRIPTION

FIG. 1 schematically depicts the device for the intermittent occlusion of the coronary sinus, wherein a multilumen catheter 1 whose distal end 2 is inserted in the coronary sinus of the heart 3 via the atrium is apparent. The proximal end 4 of the catheter 1 has a balloon inflation lumen 5 connected with a pump 6. The pressure prevailing on the distal end 2 of the catheter 1 is detected by a pressure measuring device 7, the latter also including a memory for the measured values acquired. The respectively measured pressure values are fed to a control device 8 comprising an arithmetic unit which delivers control signals via line 9 for the start and stop of the pump 6.

FIG. 2 illustrates the pressure curve determined by the measuring device 7, with the beginning of the occlusion being shown at TO and the end of the occlusion being shown at T1 and the beginning of the next occlusion being shown at T2. A number of systolic pressure peaks I0 and a number of diastolic valleys ii are to be seen. The pulse period 12 of the heart beat is represented by the time between consecutive peaks or consecutive valleys. The occlusion phase is denoted by 13 and the release phase is denoted by 14.

FIG. 3 illustrates the envelope curve 15 for the release phase 14, which connects the pressure maxima I0 and constitutes an exponential function. This exponential function 15 is defined by:

p(t)=a+b·e ^(−t/c),

-   -   a being the systolic pressure in the coronary sinus prior to the         intermittent occlusion,     -   b being the difference between the systolic pressure at the end         of the occlusion and the pressure level a,     -   c. being a time constant, and     -   t being the time measure from the beginning of the release         phase.

Departing from this exponential function 15, it is feasible to determine the lower plateau 16 of the pressure curve and, as a result, also the time required to reach the plateau value. The lowest value of the function p(t), i.e. the plateau value, is determined by equaling t=∞ (infinity). For t=∞, p(t)=a is calculated. This means that the pressure curve 15 asymptotically approaches the pressure level. It can, therefore, not be waited until the pressure curve reaches the value a, but there will be defined a multiple of this plateau value, for instance 1.01 times the plateau value that defines the time of the beginning of the next occlusion. The time at which 1.01 times the plateau value is reached, is calculated according to the following formulae:

${{p\left( t_{1.01} \right)} = {1.01 \cdot {P(\infty)}}},{{1.01 \cdot a} = {a + {b \cdot ^{\frac{t_{1.01}}{c}}}}},{t_{1.01} = {{c \cdot \ln}{\frac{b}{0.01 \cdot a}.}}}$

According to demands, the same calculation steps can be performed for other multiples of the plateau value. 

What is claimed is:
 1. A device for the intermittent occlusion of the coronary sinus, comprising: an occlusion device for the alternate occlusion of the coronary sinus and release of the occlusion, wherein the occlusion device is positioned along a distal end of a catheter that is insertable into in the coronary sinus of a heart via an atrium; a device configured to detect a bodily characteristic measurement occurring in the coronary sinus; and a control device for delivering control signals that control the time of the beginning and release of the occlusion caused by the occlusion device insertable in the coronary sinus, wherein the control device includes an arithmetic unit configured to estimate a curve of the bodily characteristic measurements detected in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the control unit is configured to trigger the next occlusion of the coronary sinus caused by the occlusion device at a time determined by the control unit as a function of the estimated curve of the bodily characteristic measurements.
 2. The device of claim 1, wherein the device configured to detect the bodily characteristic measurement occurring in the coronary sinus is a pressure detection device configured to detect fluid pressure occurring in the coronary sinus.
 3. The device of claim 2, wherein the arithmetic unit of the control device is configured to estimate a pressure curve of the fluid pressure occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, and wherein the control unit is configured to trigger the next occlusion of the coronary sinus caused by the occlusion device at the time determined by the control unit as a function of the estimated pressure curve.
 4. The device of claim 3, wherein the arithmetic unit is configured to estimate the curve of the fluid pressure from the detected pressure, said detected pressure being pressure maxima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the time for triggering the next occlusion is determined as a function of the detected pressure maxima.
 5. The device of claim 3, wherein the arithmetic unit is configured to estimate the curve of the fluid pressure from the detected pressure, said detected pressure being pressure minima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the time for triggering the next occlusion is determined as a function of the detected pressure minima.
 6. The device of claim 3, wherein the arithmetic unit is configured to estimate the curve of the fluid pressure by an exponential function based upon the detected pressure, said detected pressure being pressure maxima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the time for triggering the next occlusion is determined as a function of a plateau value of said exponential function.
 7. The device of claim 6, wherein the occlusion of the coronary sinus is released as the exponential function reaches a predefined multiple of the forecast plateau value.
 8. The device of claim 6, wherein the exponential function is defined by: p(t)=a+b·e ^(−t/c), a being the systolic or diastolic pressure in the coronary sinus prior to the intermittent occlusion, b being the difference between the systolic or diastolic pressure at the end of the occlusion and the pressure a, c being a time constant, t being the time measure from the beginning of the release phase, and p(t) being an envelope curve of the pressure maxima.
 9. The device of claim 3, wherein the arithmetic unit is configured to estimate the curve of the fluid pressure by an exponential function based upon the detected pressure, said detected pressure being pressure minima occurring in the coronary sinus during consecutive heart beats after the release of the occlusion, wherein the time for triggering the next occlusion is determined as a function of the plateau value of said exponential function.
 10. The device of claim 1, wherein the occlusion device is positioned along the distal end of the catheter which is a multi-lumen catheter.
 11. The device of claim 10, wherein the multi-lumen catheter comprises a balloon inflation lumen.
 12. The device of claim 11, wherein the balloon-inflation lumen receives fluid from a fluid pumping system.
 13. The device of claim 12, wherein the control unit delivers control signals for stopping and starting the fluid pumping system so as to control occlusions of the coronary sinus by the occlusion device.
 14. The device of claim 10, wherein the device configured to detect the bodily characteristic measurement occurring in the coronary sinus comprises a pressure measuring device positioned proximate to the distal end of the multi-lumen catheter.
 15. The device of claim 14, wherein pressure values detected by the pressure measuring device are stored in a memory that stores data indicative of the estimated pressure curve. 